JP2005328855A - Biological light measuring instrument, image display method and program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To attain an efficient performance check by shortening the reproduction time for confirming a measured video in a biological light measurement, and to delete the data during a period including noise and a period without performing a task correctly in a short time. <P>SOLUTION: The moving images of a subject in a first trial period (comprising a resting period when the subject rests and a task period in which the task is given to the subject) and a second trial period (comprising the resting period in which the subject rests and the task period in which the task is given to the subject) are picked up, and the moving image in the first trial period and the moving image in the second trial period are practically synchronized and displayed. Thus, the performance in each trial period is efficiently checked, and moving image reproduction time is shortened. Also, the data of the trial period including the noise and the trial period without performing the task correctly are deleted in a shorter time than heretofore. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  A method for displaying a result of imaging the behavior of a subject in a biological light measurement device that measures the concentration change of a metabolite inside the subject using light and visualizes the measurement result.

  A technology for measuring and imaging changes in the concentration of metabolites in a living body using light typified by near-infrared light that is highly permeable to living tissue (hereinafter, this technology is called a biological light measurement method) is patented. It describes in literature 1, patent document 2, etc., The effectiveness in the brain function measurement of these techniques is described in nonpatent literature 1, nonpatent literature 2, etc. The outline of the techniques described in these documents will be described below.

  FIG. 2 shows a configuration of an apparatus that realizes the biological light measurement method. The subject 2-1 can hope for measurement in a state where a helmet (2-2) capable of fixing a measurement optical fiber to be described later is mounted on the scalp. In the measurement optical fiber, the irradiation optical fiber (2-3) intended to irradiate the subject with the light emitted from the light source and the light passing through the living body are collected and transmitted to the detector. There is a detection optical fiber (2-4) for the purpose, and in this embodiment, five or four are used respectively. Since the tips of the irradiation optical fiber and the detection optical fiber are in contact with the scalp of the subject (2-1), the measurement can be performed in an everyday living environment without damaging the subject. . The irradiation optical fiber and the detection optical fiber are arranged, for example, at an interval of about 30 mm on the intersection of the grating. The irradiation optical fiber is connected to the light source array (2-5). In this light source array, a plurality of light sources represented by semiconductor lasers and light emitting diodes are prepared. The number of light sources corresponds to the number of irradiation optical fibers multiplied by the type of substance to be measured. The intensity of each light source is controlled by the electronic computer shown in 2-6.

  In addition, the light source array is provided with an optical coupler, and light irradiated from a plurality of light sources having different wavelengths can be incident on each irradiation optical fiber. Further, the detection optical fiber for detecting the light propagated inside the subject is connected to a detector array (2-7) having a photo detector represented by a photodiode and a photomultiplier tube. The light transmitted to the detector array is converted into an electrical signal, and the information on the passing light intensity is transmitted to the electronic computer shown in 2-6 in real time. In the electronic computer, in addition to the control of the intensity of the light source described above, the function of calculating the concentration change of the in vivo metabolite from the change in the intensity of the passing light, the time course It has a function to display as an image. The in vivo metabolites to be measured are generally oxygenated hemoglobin (Hb) and deoxygenated Hb, and are spectroscopically measured using laser beams having a plurality of wavelengths (for example, 780 nm and 830 nm). I do.

  Next, a methodology for measuring and imaging blood volume changes accompanying brain activity will be described (FIG. 3). FIG. 3 shows a diagram in which two irradiation optical fibers are arranged on both sides of one detection optical fiber in the arrangement method of the irradiation optical fiber and the detection optical fiber shown in FIG. Reference numerals 3-1 and 3-2 denote light sources, and the intensity is modulated at different frequencies. Reference numeral 3-3 denotes an irradiation optical fiber, and 3-4 denotes a detection optical fiber, which are arranged at intervals of 30 mm. Reference numerals 3-5 and 3-6 show the brain structure in a simplified manner, and show a skull and a cerebral cortex, respectively. Moreover, the banana-shaped area | region shown to 3-7 has shown the path | route of the light which propagated each optical fiber for irradiation-optical fiber for a detection. Since biological tissue (especially the skull) is a strong scatterer, the light irradiated by the irradiation optical fiber loses directivity from the irradiation position and is scattered in all directions. Among them, the light propagating between the light irradiation position and the light detection position 30 mm apart can propagate in a banana shape and can be detected as reflected light as shown in the figure. The detected light is converted from an optical signal to an electrical signal by a detector (consisting of a photodiode, a photomultiplier tube, etc.) shown in 3-8. The converted electric signal is processed by the lock-in amplifier shown in 3-9.

  By this method, the reflected light intensity of the light emitted from the two light sources can be detected simultaneously and discriminated independently. Here, when the concentration of oxygenated Hb or deoxygenated Hb changes with brain activity at any location in region 1 or region 2, the intensity of reflected light changes. Therefore, the blood volume change in the region 1 and the region 2 can be calculated from the intensity of the reflected light. In FIG. 3, there are two pairs of the irradiation optical fiber and the detection optical fiber, and one of these will be described. The light intensity reaching the detection optical fiber at each time is defined as I (t). In this biological light measurement method, in order to measure the concentration change of the metabolite in the living body, state 0 and state 1 are assumed, and the light intensity in each case is set to I0 and I1. Here, the state 0 and the state 1 are, for example, a reference state represented by a state of being rested in the state 0. In the state 1, it is assumed that the motor area is active by the state of moving the finger. For each two-wavelength light source used for measurement, the change in absorbance (ΔA (t)) inside the living body at each time satisfies the following relational expression.

Here, L in Formula 1 indicates an average optical path length between the light source and the detector. Further, εoxy and εdeoxy in the formulas indicate molecular extinction coefficients of oxygenated Hb and deoxygenated Hb, respectively. By applying Equation 1 to each wavelength, changes in the concentration of oxygenated Hb and deoxygenated Hb associated with brain activity (ΔCoxy, ΔCdeoxy, respectively)

It becomes. In practice, it is difficult to determine L, so

For C ′, which is a unit having a dimension obtained by multiplying density by distance,

Is calculated.

  Next, a measurement method using this FIG. 3 and a method for creating a topographic image showing the distribution of concentration changes of oxygenated Hb and deoxygenated Hb calculated using Equation 4 will be described (FIG. 4). In FIG. 4, five irradiation optical fibers are placed at positions 21, 22, 23, 24, and 25 in the figure, and similarly four detection optical fibers are shown in 31, 32, 33, and 34 in the figure. The case where it arrange | positions to each position of number is shown. In such an arrangement, there are many pairs of irradiation optical fibers and detection optical fibers. Among these, there are a total of 12 pairs in which the irradiation optical fibers and the detection optical fibers exist at intervals of 30 mm. To do. The midpoint of these optical fiber pairs is defined as a sampling point, which is a position that gives position information on the concentration change of oxygenated Hb and deoxygenated Hb detected by one optical fiber pair. Under this assumption, there are a total of 12 sampling points (4-1) in FIG. A topographic image shown in FIG. 5 is obtained by performing spatial interpolation processing on the oxygen concentration Hb and deoxygenation Hb concentration changes at these 12 points. This topography means a topographic map, and displays physical quantities in a different dimension from the coordinates on the plane coordinates. In addition, the measurement system shown in FIG. 3 can sample data on the order of 100 milliseconds, and can also make a moving image at this sampling interval.

  Next, the activation method (paradigm) used to activate the brain will be described. In this living body optical measurement method, a problem is imposed on the subject in order to cause a change in the concentration of the metabolite in the living body. An example of this paradigm and task sequence is shown in FIG. In the figure, T and R mean a task period (period in which the task is executed) and a rest period (state in which the state of brain activity is different from the task period, such as standing still), respectively. For example, to explain using the human hand shown in FIG. 7, in the task period, the subject executes a task of randomly bringing the index finger, middle finger, ring finger, and little finger other than the thumb and thumb into contact at a speed of 1 Hz. On the other hand, in the rest period, unlike the task period described above, the rest period is maintained without touching each finger. The difference between the task period and the rest period is only whether or not finger movement is performed. As a result, the finger motor area existing in the temporal region is activated, and the concentration of oxygenated Hb at the active site changes. It is described in Non-Patent Document 3 and the like. In actual measurement, the T and R times are set to various values depending on the inspection purpose and contents, but generally, T = 15 seconds and R = 30 seconds. Further, in order to reduce the noise of the measured signal, the task is repeatedly executed, and a synchronous addition process is performed on the measured reflected light intensity change. The number of repetitions of T used in actual clinical practice is about 5 to 10 times, and the time required for measurement is about 10 minutes.

  FIG. 8 is a measurement scene using an actual measurement device. The light source array and detector array shown in FIG. 2 are housed in the housing (8-1), and the fiber array (8-2) that combines the irradiation optical fibers and the detection optical fibers is covered. It is connected to a helmet (8-4) arranged on the head of the specimen (8-3). Further, an electronic computer (8-5) is provided on the casing, and the measurement result can be quickly browsed by the printer (8-6) for printing the measurement result. Further, since the optical fiber array described above is connected to the support column (8-7) that supports the printer and the casing is provided with casters (8-8), it has high portability. For this reason, it is possible to freely set the positional relationship between the subject and the measurement device, and it is possible to measure the subject not only in the laboratory for outpatients of medical institutions, but also in operating rooms and hospital rooms. It has become.

JP-A-8-103434

JP-A-9-98972 E Watanabe, A Maki, F Kawaguchi, Y Yamashita, H Koizumi, Y Mayanagi, "Noninvasive Cerebral Blood Volume Measurement During Seizures Using Multichannel Near Infrared Spectroscopic Topography.", Journal of Biomedical Optics, 2000, July, 5 (3), P . 287-290. (Watanabe, Maki, Kawaguchi, Yamashita, Koizumi, Mayanagi. “Measurement of noninvasive blood volume change during neurological seizure period by topography method applying near infrared spectroscopy”, Medical Engineering Optics, 2000, 7 Monthly issue (pages 287 to 290)) E. Watanabe, A. Maki, F. Kawaguchi, K. Takashiro, Y. Yamashita, H. Koizumi, and Y. Mayanagi, "Non-invasive assessment of language dominance with Near-Infrared Spectroscopic mapping", Neurosci. Lett. 256 (1998), (Watanabe, Maki, Kawaguchi, Takashiro, Yamashita, Koizumi, Mayanagi. “Measurement of non-invasive language dominant hemisphere by near infrared spectroscopy”, Neuroscience, 1998) Atsushi Maki, Yuichi Yamashita, Yoshitoshi Ito, Eijiyu Watanabe, Yoshiaki Mayanagi, and Hideaki Koizumi, “Spatial and tempr. 22 (No. 12), pp. 1997-2005 (1995). (Atsushi Maki, Yuichi Yamashita, Yoshitoshi Ito, Aige Watanabe, Yoshiaki Mayanagi, Hideaki Koizumi, “Spatio-temporal analysis of the activated state of the human motor cortex”, Medical (Physics, Volume 22 (12), 1997-2005 (1995))

  In the biological light measurement method, the same task (problem) may be repeatedly performed a plurality of times in order to reduce noise in the measurement result, but the following two states can be considered during the examination of the subject. In the first state, a task instructed by a doctor or laboratory technician is executed during the task period, and the patient is kept resting during the rest period as instructed. In this case, it is possible to evaluate the brain activity of the subject if the doctor or the laboratory technician analyzes the data after the measurement is completed. On the other hand, as a matter of course, there is a case where the user performs an action different from the instruction during the task period or the rest period. For example, when coughing during measurement, the state of contact of the helmet with the head changes, so noise (artifact) is detected. Also, if the task is simple, the subject gets bored and goes to sleep, or the subject moves another task (for example, moves the left hand, even though the exercise of the right hand is used as the task) ) May be implemented, and in this case, it may not be detected as noise (artifact). In this way, if the subject performs a task that is not detected as an artifact and that is different from the instructions of the doctor or laboratory technician, a location that is different from the intended brain function site is activated, and the correct test result is obtained. It may be impossible.

If data for a period in which noise is detected as described above or data for a period in which noise is not detected but a correct task is not executed is used for data analysis, correct data cannot be obtained. Thus, in order to obtain correct data, it is necessary to specify the period in which noise occurs in this way and exclude it from the target of synchronous addition. However, a method for efficiently performing this has not been established.
On the other hand, a method of recording and photographing the state of the subject being measured on a video is conceivable. A VTR camera can be introduced and implemented in an embodiment as shown in FIG. Unlike magnetic resonance imaging devices and magnetoencephalographs that require a special laboratory for measurement, the biological light measurement method does not need to be aware of electromagnetic noise. For this reason, the VTR camera (9-1) can be disposed in the vicinity of the measurement apparatus, and the VTR camera can be installed at an arbitrary position with respect to the subject. For this reason, for example, taking the measurement of the finger movement function described with reference to FIG. 9 as an example, it is possible to image only the finger movement of the subject or the entire subject. .

  10-1 in FIG. 10 is a time course indicating the measurement result, and in this figure, changes in reflected light intensity of each wavelength at each sampling point are shown. Reference numeral 10-2 denotes an image obtained by photographing the behavior of the subject. The bar (10-3) in 10-1 described above clearly shows the correspondence between the playback time of the video and the time on the time course. By playing back the video and the time course synchronously, It is possible to check existing problems while comparing them with the video.

However, even if the photographed result and the measurement result are reproduced in a synchronized manner as shown in FIG. 10, it is not an effective means for a doctor or a laboratory technician. This is because, after processing the measurement result, a topography image as shown in FIG. 7 can be obtained within a few minutes after the end of the measurement, but the image shown in 10-2 is about 10 minutes from the start to the end of the measurement. This is because it is necessary to reproduce and check all, and the measurement result cannot be confirmed as soon as the measurement is completed. In addition, video results between tasks cannot be directly compared, and an efficient performance check cannot be performed.
Therefore, these problems are solved, the playback time for checking the measurement video is shortened, and an efficient performance check is possible, and data in a period that includes noise or a period in which tasks are not performed correctly is obtained in a short time. We examined how to delete it.

  As means for solving the above problems, in the present invention, a first trial period (having a rest period in which the subject is resting and a task period in which a task is given to the subject) and a second trial period (the subject is resting). A moving image of the subject in the first trial period and a moving image in the second trial period are substantially synchronized. Provided is a biological light measurement device characterized by being displayed. As a result, the performance check can be performed in the time required for one trial period, and the video data or measurement data between the tasks can be directly compared.

  According to the present invention, since the measurement state and measurement result of the subject in each trial period are confirmed at the same time, the performance check in each trial period can be efficiently performed, and the moving image reproduction time can be shortened. In addition, it is possible to delete data of a trial period including noise or a trial period in which a task is not correctly performed in a shorter time than before.

  One embodiment for carrying out the present invention will be described in a first embodiment. First, a measurement implementation method and a measurement result processing method will be described with reference to the flowchart shown in FIG. First, when the sequence shown in FIG. 6 is used, a task period (T), a rest period (R), and the number of task repetitions (n) are set in advance. In this embodiment, it is assumed that n = 5 following FIG. The rest and the task are alternately repeated n times based on the set number of times and time. When the measurement is completed, first, the measurement data is saved. This measurement data is a time change characteristic of reflected light intensity of each wavelength at each sampling point. Subsequent to storing the measurement data, the video data captured during the measurement period is also stored. Here, both measurement data and video data are time-series data, but the recording time of each data is aligned so that the synchronization of each data can be maintained, the time when the measurement is started, the time when the task is started The end time is also recorded in both data as a marker. Next, the video data is divided and stored for each measurement sequence. there,

5 video files including each period are stored in a folder.

  These storage states are shown in FIG. In this folder, in addition to the captured video file “all video 1”, “video 1 (Task 1)”, “video 1 (Task 2)”, “video 1 (Task 3)”, “video 1 (Task 4)”, “Video 1 (Task 5)” is stored. These files are used in the screen configuration shown in FIG. 1 when performing “synchronized playback of video data or measurement data for each task” in the flowchart shown in FIG. In the screen configuration shown in FIG. 1, the time course of measurement data shown in 1-1 and the video screen shown in 1-2 are displayed side by side. In this embodiment, five video screens are arranged in the order of the first task, the second task,..., The fifth task in order from the top. Bars indicated by 1-3 and 1-4 indicate a rest period and a task period, respectively. The arrows 1-5 indicate the display times of the videos shown in 1-2, and the videos are played back substantially in synchronization (substantially here, mechanical noise). It means that it is acceptable to have a difference in synchrony due to the performance limit of the machine or the machine, and that it does not exceed the perception that the user is synchronized.) In other words, the five images have the task start times (explained using the measurement sequence shown in FIG. 6, the first t2, the second t4, the third t6 for each of the five images. 4th t8 and 5th t10)) are reproduced at the same time.

  On the other hand, since the time course shown in 1-1 is time-series data, the rest period and the task period are alternately set as shown in FIG. 6, and the task period and rest shown in 1-6-1 are set. It is displayed in the period display bar. The line indicated by 1-7 moves in synchronization with the arrow indicated by 1-5. In this way, the line indicating the relationship between the video and the time at which the video is displayed moves synchronously on the video and the time course, so that the user can clearly grasp the relationship between the data indicated by the time course and the video. It becomes possible to do. Reference numeral 1-8 denotes a check box, and a check mark is recorded in this embodiment. This is because the behavior of the subject in the third task is significantly different from the first, second, fourth, and fifth tasks in the third task, and is excluded from synchronous addition when performing data processing. The scene selected by the user is shown.

  Simultaneously with the input to this check box, the line indicating the time synchronism shown in 1-9 becomes a line type different from the other lines, and the invalidity of the data on the time course can be conveyed to the user. In the display method shown in FIG. 1, when T = 15 seconds, R = 30 seconds, and the number of task repetitions is 5 (see the sequence shown in FIG. 6), the display time of 255 seconds is 75 seconds ( 30 + 15 + 30). Also, the lines indicated by 1-11 are the time series change (time course) of the detected light intensity obtained by converting the detected light described in FIG. 3 into an electrical signal. Each line indicates the sampling point shown in FIG. It corresponds to the measurement data in (4-1) (in this embodiment, there are 12 lines (1-11) corresponding to 12 sampling points (4-1)). 1-10 indicates how many seconds each line shown in 1-7 and 1-9 is after the start of the task, and the time of each line, and the position of each line shown in 1-7 and 1-9. In synchronization with the change, the displayed time changes.

  Next, a modification of FIG. 1 will be described with reference to FIGS. In FIG. 12, it is automatically determined that there is noise in the data displayed as the time course (12-1), and the task having the noise is not displayed as a video, or the measurement data of the task is excluded from the synchronous addition. The embodiment which features is shown. As an example of a determination algorithm in the case where there is noise, an example in which it is determined that there is noise when a change in blood volume per unit time exceeds a preset threshold value (m) can be given. 12-2 is a threshold value setting part which inputs the threshold value. As an example, if “0.2 mM · mm / 0.1 sec” is input, and a blood volume of ± 0.2 mM · mm changes in 0.1 seconds, it is regarded as noise. The calculation of the blood volume change uses a calculation algorithm shown in Equations (1) to (4). In the present embodiment, noise is generated at the sampling points indicated by 12-3, and the measurement in the fourth task including this time is invalid. For this reason, an image is not displayed in the place indicated by 12-4. Further, the measurement data in the fourth task can be excluded from the synchronous addition.

  FIG. 13 is a modification of FIG. 1 and FIG. The video screen in each task period and the topographic image (13-1) obtained by synchronously adding the measurement data in each task period are displayed side by side, and an image in the case of reproducing substantially synchronously is shown. In this embodiment, it is possible to select a task (any one of five tasks) to be excluded from the synchronous addition while viewing the video, and it is possible to immediately see the topography image created based on the selected result. By using the method shown in this embodiment, for example, it becomes possible for the user to easily compare the difference in topographic moving images between when the third task is added and when the task is removed. The data processing method can more easily reflect the check result. Of course, it is possible to check and select a task used for synchronous addition. Here, in the drawing shown in the present embodiment, a check is entered for the third task. Therefore, the passing light intensity of each channel in each period of t1 ≦ t4, t3 ≦ t6, t7 ≦ t10, t9 ≦ t12 shown in Equation 5 is synchronously added, and ΔC ′ is calculated using Equations 1 to 4. By performing spatial interpolation using the position information of each channel, a topographic image can be displayed as shown in 13-1 of this figure.

FIG. 14 is a modification of FIG. 13 and displays the topographic image (14-1) side by side for each task that has been repeatedly performed. As shown in 14-2, in the figure, the check box is checked for the third task. For this reason, only the third topography image is not displayed. As a result, by displaying only the first, second, fourth, and fifth topography images to be measured, the number of images that the user needs to check can be reduced.
Note that the above-described image display and data processing can also be executed by installing a program for executing these functions in a conventional biological light measurement device that does not have these functions.

Since the biological light measurement method uses light, there is no interference with other electromagnetic energy. For this reason, simultaneous measurement with a measuring device using electromagnetic energy other than light is possible. One embodiment will be described below.
FIG. 15 shows a configuration of the living body light measurement device shown in FIG. 9 and a device in which another living body measurement device is added to the living body light measurement device. In this embodiment, a case where another finger movement function measuring device (15-2) is installed beside the biological light measuring device (15-1) will be described, but of course, the present invention is not limited to this embodiment. Absent. The subject (15-4) wearing the helmet (15-3) is connected to the biological light measurement device by an optical fiber array (15-5). Further, a sensor (15-6) is connected to the finger of the subject, and this sensor is connected to the finger movement function measuring device. In addition, a video imaging device (15-7) is provided on the biological light measurement device, and the behavior of the subject can be imaged.

  Next, the configuration of the finger movement function measuring device will be described with reference to FIG. An AC voltage having a predetermined frequency (for example, 20 kHz) is generated by the AC generation circuit (16-1). The generated AC voltage having a predetermined frequency is converted into an AC current having a predetermined frequency by the current generating amplifier circuit (16-2). The alternating current is passed through the transmitting coil 2 attached to the living body. The magnetic field generated by the transmitting coil (16-3) generates an induced electromotive force in the receiving coil (16-4) attached to the living body. The generated electromotive force (having the same frequency as the AC voltage having a predetermined frequency generated by the AC generation circuit (16-1)) is amplified by the preamplifier circuit (16-5). The amplified signal is input to the detection circuit (16-6). In the detection circuit, in order to detect at a predetermined frequency or double frequency generated by the AC generation circuit, the phase of the output of the AC generation circuit is adjusted by the phase adjustment circuit (16-7), and then the reference signal The signal is input to the reference signal input terminal of the detection circuit 4 as (16-8).

  It should be noted that the phase adjustment circuit (16-7) is not necessarily required when detecting at twice the predetermined frequency. As a simple circuit configuration for detecting at a double frequency, the predetermined frequency of the AC generation circuit (16-1) is set to a double frequency, converted to a half frequency by a division cycle, and then a current generation amplifier circuit (16 -2), and a reference signal (16-8) is supplied with a signal having a frequency twice the predetermined frequency of the AC generation circuit (16-2) at the reference signal input terminal of the detection circuit (16-6). The configuration is to be input. The output of the detection circuit (16-6) is amplified by an amplifier circuit (16-10) to obtain a desired voltage after passing through a low-pass filter circuit (16-9). , Output (16-11) is obtained. The output (16-11) is input to the computer as digital data by an analog-digital conversion board (AD board) built in the computer (16-12). With the configuration example described above, a voltage corresponding to the relative distance D between the receiving coil (16-4) and the transmitting coil (16-3) attached to the living body can be detected. A method of mounting the finger movement function measuring device on a living body will be described with reference to FIG.

  The transmitting coil (17-1) is attached to the upper part of the thumb, and the receiving coil (17-2) is attached to the upper part of the index finger. The transmitting coil is wound around a coil mounting member (17-3) and connected to the current generating amplifier (16-2) shown in FIG. Moreover, each mounting part is attached to the band (17-4), and it is set as the structure which can absorb an individual difference of the magnitude | size (thickness) of a finger | toe using rubber | gum or sponge. In the configuration shown in this figure, an output corresponding to the relative distance D between the thumb and the index finger can be obtained. Moreover, the finger | toe which mounts a receiving coil and a transmitting coil is not limited to a thumb or an index finger, You may mount a receiving coil or a transmitting coil in arbitrary fingers. In addition, the transmitting coil and the receiving coil are attached to the upper lip and the lower lip of the lips, and the movement associated with the movement of the mouth can be detected.

  When these springs are attached to the thumb and forefinger, and patients with Parkinson's disease are instructed to perform finger tapping between the thumb and forefinger (repeating the opening and pulling of the thumb and forefinger) as quickly as possible. Fig. 18 shows the waveforms actually obtained. It should be noted that the relationship between the potential difference obtained from the distance between the two coils and the actual distance between the thumb and the index finger has been obtained in advance, and the waveform shown in FIG. 18 is a calibrated characteristic. In FIG. 18, the waveform indicated by 18-1 is the data converted into the relative distance D and the velocity waveform (data of the first derivative waveform (dX / dt) in the time direction of the distance X). Indicates. In FIG. 19 in which the figure is enlarged from 0 to 3 seconds, the measurement data and the velocity waveform are similarly shown in 19-1 and 19-2. T1 and T2 shown in 19-2 indicate the time width in which the time difference between adjacent maximum peaks in the velocity waveform is detected and the time width in which the time difference between adjacent minimum peaks in the velocity waveform is detected.

  The figure which plotted this T1 and T2 for every tapping frequency is shown (FIG. 20). 20-1 and 20-2 plot the times of T1 and T2 for each tapping frequency. From this figure, it can be seen that T1 is finger tapped around 0.4 seconds. On the other hand, in T2, although a change is recognized centering on 0.4 second, which is substantially the same as T1, it can be seen that fluctuations occur in several places. As shown in FIG. 18, by plotting the time variation of tapping, it becomes possible to visually understand the temporal fluctuation of tapping.

  Since the measurement apparatus shown in FIG. 15 includes a video camera, the biological light measurement apparatus capable of simultaneously measuring the measurement result using the biological light measurement apparatus and the biological light measurement apparatus shown in FIG. If the results of other biological measuring devices and the results of further imaging are displayed and reproduced at the same time, the measurement results from the respective biological measuring devices and the performance check of the subject can be performed simultaneously. The display method is shown in FIG. In this figure, the time course (21-1) showing the result of measurement using light, the finger movement waveform (21-2) obtained from the finger movement function measuring apparatus shown in FIG. 15, and the imaging result of the subject ( 21-3). In addition, a line (21-4) indicating the relationship between the task, the rest period, and the display time is described at the bottom of the image so that the display time can be understood. The location of this line changes over time, and each of the five images is reproduced substantially synchronously. In this figure, the time course (21-1) indicating the result of measurement using light, the finger movement waveform (21-2) obtained from the finger movement function measuring device, and the imaging result (21-3) of the subject are all shown. Although one is displayed, any one or two of these may be displayed.

As a result, it is possible to simultaneously measure biological functions using multiple modalities, and to compare the behavior of the subject for each repeated task, making diagnosis easier for doctors and laboratory technicians. It can be a measurement system. That is, in this embodiment, in addition to the imaging information of the subject, the reliability of data can be improved by directly measuring the motion, movement, motion, phase change information, etc. of the subject, for example.
In addition, the biological light measurement method can be measured simultaneously with other biological measurement methods (brain waveform, functional magnetic resonance drawing device, positron emission tomography), and this advantage is also realized by the biological light measurement method with VTR. it can. For this reason, it is possible to expand the types of physiological information that can be acquired.

  In a biological optical measurement device that measures changes in the concentration of metabolites in the living body, such as changes in blood volume due to brain activity, it is easy and quick to compare the calculation result of the concentration change and the behavior of the subject. It becomes possible to carry out on time.

The screen block diagram (1) of the biological light measuring device provided by this invention. Device configuration of the biological light measurement device. A method for measuring changes in blood volume associated with brain activity. A method for creating a topography image showing the distribution of changes in concentration of oxygenated Hb and deoxygenated Hb. Topography image. Task sequence for performing brain function measurement. Human hand. Measurement of brain activity using a biological light measurement device. The apparatus structure of the biological light measuring device which comprises a VTR camera. The display method of the result and VTR which image | photographed the test subject in a prior art. Measurement implementation method and measurement result processing method. The screen block diagram (2) of the biological light measuring device provided by this invention. The screen block diagram (3) of the biological light measuring device provided by this invention. The screen block diagram (4) of the biological light measuring device provided by this invention. The apparatus block diagram of the measuring device which has the imaging function of the test object in the apparatus which provided another living body measuring device different from this living body light measuring device and this living body light measuring device. Configuration of a finger movement function measuring device. A method for attaching a finger movement function measuring device to a living body. Finger movement waveform (1). Finger movement waveform (2). Time change of T1 and T2. The screen structure of the measuring device shown in FIG. Storage folder for video data.

Explanation of symbols

1-1: Time course of measurement data, 1-2: Video screen, 1-3: Bar indicating rest period, 1-4: Bar indicating task period, 1-5: 1-2 Display time, 1-6-1: Task period and rest period display bar, 1-6-2: Task period, 1-6-3: Rest period, 1-7: Line indicating time synchronization, 1-8 : Check box, 1-9: Line indicating the synchronization of the time when the check box of 1-8 is selected, 1-10: Time display box, 1-11: Time series change of detected light intensity at each sampling point 2- 1: Subject, 2-2: Helmet, 2-3: Optical fiber for irradiation, 2-4: Optical fiber for detection, 2-5: Light source array, 2-6: Computer, 2-7: Detector array 3-1: Light source, 3-2: Light source, 3-3: Optical fiber for irradiation, 3-4: Detection Optical fiber, 3-5: skull, 3-6: cerebral cortex, 3-7: irradiation optical fiber-path of light propagated through detection optical fiber pair, 3-8: detector, 3-9: lock In-amplifier, 4-1: Sampling point, 8-1: Housing, 8-2: Fiber array including irradiation optical fiber and detection optical fiber, 8-3: Subject, 8-4: Helmet 8-5: Computer, 8-6: Printer, 8-7: Supporting column for supporting the printer, 8-8: Caster, 9-1: VTR camera, 10-1: Time course showing measurement results, 10-2 : Image of subject's behavior imaged, 10-3: Bar in 10-1, 1-1: Time course, 1-2: Multiple video screens, 1-3: Rest period, 1-4: Task period 1-5: arrow, 1-6: task period, rest period display bar, 1-7: Line, 1-8: Check box, 1-9: Line indicating time synchronism, 12-1: Time course, 12-2: Threshold setting unit, 12-3: Noise occurrence location, 12- 4: video non-display area, 13-1: topography image, 14-1: topography image, 14-2: check box, 15-1: biological light measurement device, 15-2: finger movement function measurement device, 15-3 : Helmet, 15-4: Subject, 15-5: Optical fiber array, 15-6: Sensor, 15-7: Video imaging device, 16-1: AC generation circuit, 16-2: Amplifier circuit for current generation, 16-3: Transmitting coil, 16-4: Receiving coil mounted on the living body, 16-5: Preamplifier circuit, 16-6: Detection circuit, 16-7: Phase adjustment circuit, 16-8: Reference signal, 16-9: Low-pass filter (L w-Pass filter) circuit, 16-10: amplifier circuit, 16-11: output, 16-12: computer, 17-1: coil for transmission, 17-2: coil for reception, 17-3: coil mounting member, 17-4: Band, 18-1: Waveform of data converted into relative distance D, 18-2: Speed waveform of 18-1, 19-1: Waveform, 19-2: Speed waveform of 18-1, 20- 1: Time change of T1, 20-2: Time change of T2, 21-1: Time course showing the result of measurement using light, 21-2: Finger obtained from the finger movement function measuring device shown in FIG. Movement waveform, 21-3: imaging result of subject, 21-4: line indicating the relationship between task, rest period and display time.

Claims (20)

A light irradiator for irradiating the subject with light;
A photodetector for detecting light emitted from the light irradiator and propagated in the subject;
From the measurement result detected by the photodetector, a calculation unit that calculates a change in the metabolite concentration of the subject,
An imaging device that captures a moving image of the subject during measurement;
The change in the metabolite concentration in the first trial period and the second trial period is measured, and each of the first trial period and the second trial period includes a rest period in which the subject is resting and the subject. Has a task period to give a task to the specimen,
A biological light measurement apparatus comprising: a display device that displays the moving image in the first trial period and the moving image in the second trial period substantially in synchronization.   The biological light measurement device according to claim 1, wherein the display device displays an image displaying the change in metabolite concentration and the moving image substantially in synchronization.   The biological light measurement device according to claim 2, wherein the display device displays the change in the metabolite concentration as a topography image.   The biological light measurement apparatus according to claim 2, further comprising a setting unit configured to set whether to display the moving image for each trial period or not.   5. The display device according to claim 4, wherein the display device adds and averages the change in metabolite concentration during a trial period selected to be displayed by the setting unit, and displays the change in metabolite concentration averaged. Biological light measurement device.   The biological light measurement device according to claim 5, wherein the display device displays the change in metabolite concentration as a topography image. The calculation unit adds and averages the change in metabolite concentration during the trial period in which the change in metabolite concentration during the trial period does not exceed a predetermined threshold,
The biological light measurement device according to claim 2, wherein the display device displays the concentration change of the metabolite concentration averaged.   The biological light measurement apparatus according to claim 7, further comprising a setting unit that sets the threshold value.   The biological light measurement device according to claim 7, wherein the display device displays the change in metabolite concentration averaged and averaged as a topography image.   The biological light measurement apparatus according to claim 1, further comprising a setting unit configured to set a time for the rest period, a time for the task period, and a number of times the task is given to the subject.   The biological light measurement device according to claim 1, further comprising a measurement device that measures the movement of the subject using a sensor mounted on the subject.   The display device synchronously displays an image displaying the change in metabolite concentration and measurement data obtained by the measurement device, or the moving image and measurement data obtained by the measurement device. The biological light measurement device according to claim 11. Irradiating the subject with light; and
Detecting light propagated in the subject;
Calculating a change in the metabolite concentration of the subject from the detected light propagated in the subject;
Capturing a moving image of the subject during measurement,
The change in the metabolite concentration in the first trial period and the second trial period is measured, and each of the first trial period and the second trial period includes a rest period in which the subject is resting and the subject. Has a task period to give a task to the specimen,
Displaying the moving image in the first trial period and the moving image in the second trial period substantially synchronously;
And a step of selecting which metabolite concentration change in the trial period is used for the addition average when the metabolite concentration change for each trial period is added and averaged.   The image display method according to claim 13, further comprising a step of displaying the metabolite concentration change averaged.   The image display method according to claim 13, further comprising a step of setting whether to display or not display the moving image for each trial period. A program used in a biological light measurement device for measuring a change in metabolite concentration of a subject in a first trial period and a second trial period,
Each of the first trial period and the second trial period has a rest period in which the subject rests and a task period in which a task is given to the subject,
A program for causing a computer to execute a step of displaying a moving image during measurement of the subject in the first trial period and the moving image in the second trial period substantially in synchronization.   17. The program according to claim 16, wherein the metabolite concentration change and the moving image are displayed substantially in synchronization. Adding and averaging the change in metabolite concentration during the trial period in which the change in metabolite concentration during the trial period does not exceed a predetermined threshold;
The program according to claim 16, further comprising a step of displaying the change in metabolite concentration averaged and the moving image substantially in synchronization.   The program according to claim 18, wherein the threshold value is a variable value that can be set.   19. The program according to claim 18, wherein the addition-averaged change in the metabolite concentration is displayed as a topography image.